Apparatus and method to assess airway clearance therapy efficacy

ABSTRACT

A respiratory device may include an inlet port and an outlet port. A fluid pathway may extend between the inlet port and the outlet port. A filter housing may be positioned between the inlet port and the outlet port. A filter may be positioned within the filter housing. A first pressure port may be positioned on an inlet side of the filter housing. A second pressure port may be positioned on an outlet side of the filter housing. The first pressure port and the second pressure port may extend parallel to the fluid pathway. A pressure transducer may be coupled to the first pressure port and the second pressure port and configured to measure a pressure drop between the first pressure port and the second pressure port.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority under 35 U.S.C. § 119(e) to U.S.Provisional Patent Application Ser. No. 62/694,115, filed Jul. 5, 2018,which is expressly incorporated by reference herein.

BACKGROUND

The present disclosure relates to respiratory devices. Moreparticularly, the present disclosure relates to a respiratory device andmethod for assessing airway clearance therapy efficacy.

There is no good objective/standard method to assess airway clearancetherapy efficacy at home for both clinicians and patients. The need torationalize the utilization of health care resources together with theoptimization of patient's care has prompted the development of models ofassistance based on home monitoring. At the present time, most of thesuggested models are based on the utilization of diaries for symptomsperceived by the patients. Even if positive results are reported interms of reductions in hospitalization, many patients tend tounderestimate the severity of their condition and their compliance inrecording their symptoms rapidly decreases with time. There is nofrequent/close monitoring for patients who receive airway clearancetherapy at home. Attempts of using more objective measurements such ashome spirometers have been done but poor results have been reportedmainly due to the difficulties in performing a spirometric test withoutmedical supervision.

More often than not, patients do spirometry in clinics every 3-6 monthsduring follow-up sessions. During gaps, there is no way for cliniciansto track the patient's lung condition and the patient's interaction withairway clearance therapy. Even for a spirometric test done in a lab,spirometry appears to be a very effort-dependent test and sometimesclinicians do not even trust its results. Spirometry is not suitable forcertain populations such as young kids, the elderly, and patients withNeural muscular disease (NMD). In such scenarios, clinicians have torely on the patients' self-declaration about their conditions.

One technique in assessing airway clearance therapy efficacy is based onmeasuring the impedance of the patient's lung through sensing of theflow and pressure drop while sending pressure pulses into the patient'slung and evaluating a modulation effect by the lung. In thismeasurement, there are lots of potential events that could lead tocontamination of the flow rate/pressure drop signal, which could destroythe accurate interpretation of lung impedance. Those potential eventsare mainly unexpected artifacts such as leakage, blockage, coughing,burping, swallowing, hemming, etc. These events will either artificiallyincrease or decrease the impedance readings and need to be identified inthe signal and rejected.

SUMMARY

The present disclosure includes one or more of the features recited inthe appended claims and/or the following features which, alone or in anycombination, may comprise patentable subject matter.

In one aspect of the disclosed embodiments, a respiratory device mayinclude an inlet port and an outlet port. A fluid pathway may extendbetween the inlet port and the outlet port. A filter housing may bepositioned between the inlet port and the outlet port. A filter may bepositioned within the filter housing. A first pressure port may bepositioned on an inlet side of the filter housing. A second pressureport may be positioned on an outlet side of the filter housing. Thefirst pressure port and the second pressure port may extend parallel tothe fluid pathway. A pressure transducer may be coupled to the firstpressure port and the second pressure port and configured to measure apressure drop between the first pressure port and the second pressureport.

It may be desired that the filter is positioned between the firstpressure port and the second pressure port. The filter may include ascreen. A gasket may extend around the filter. The gasket may seal aninlet side and an outlet side of the filter. The gasket may preventairflow around the filter.

It may be contemplated that the inlet port is coupled to a respirator.The filter housing may include an inlet segment including the inlet portand an outlet segment including the outlet port. The inlet segment andthe outlet segment may be coupled together. A clamp may be provided tocouple the inlet segment to the outlet segment. The clamp may seal theinlet segment to the outlet segment.

In another aspect of the disclosed embodiments, a method of assessingairway clearance therapy efficacy may include generating a pressurepulse in a respiratory device being used by a patient. The method mayalso include measuring the patient's lung impedance during the pressurepulse. The method may also include assessing the patient's lungcondition based on the patient's lung impedance. The method may alsoinclude delivering airway clearance therapy to the patient. The methodmay also include assessing the patient's lung condition after the airwayclearance therapy. The method may also include comparing the patient'slung impedance to the patient's lung condition after the airwayclearance therapy to determine a therapy efficacy.

In some embodiments, the method may also include deriving the patient'slung resistance and lung compliance from the patient's lung impedance.The method may also include assessing the patient's lung condition basedon the patient's lung resistance and lung compliance. The patient's lungcompliance may be a factor of the patient's lung inertia. The method mayalso include deriving an overall resistance of a patient's respiratorysystem based on a graph of the patient's lung resistance. The method mayalso include deriving a resistance of a patient's conducting airwaysbased on a graph of the patient's lung resistance.

Alternatively or in addition to, the method may also include deriving apatient's lung reactance from the patient's lung impedance. The methodmay also include determining a compliance of the patient's lung based onthe patient's lung reactance.

Optionally, the method may also include comparing the patient's lungimpedance to the patient's lung condition after the airway clearancetherapy to determine a therapy efficacy further comprises comparing thepatient's lung impedance before the airway clearance therapy to thepatient's lung impedance after the airway clearance therapy.

In some embodiments, the method may also include detecting a deviationin a baseline of a breathing signal. The method may also include findinga new baseline for the breathing signal. The method may also includeupdating the baseline for the breathing signal to the new baseline. Thedeviation may be greater than 13 percent. The method may also includerejecting detected artifacts with a continuous presence of less than twodata points. The method may also include mapping a breathing waveformonto a real time impedance curve to identify intact breathing cycles.The method may also include connecting the intact breathing cycles tocalculate the patient's lung impedance.

Additional features, which alone or in combination with any otherfeature(s), such as those listed above and/or those listed in theclaims, can comprise patentable subject matter and will become apparentto those skilled in the art upon consideration of the following detaileddescription of various embodiments exemplifying the best mode ofcarrying out the embodiments as presently perceived.

BRIEF DESCRIPTION OF THE DRAWINGS

The detailed description particularly refers to the accompanying figuresin which:

FIG. 1 is a front perspective view of a respiratory device;

FIG. 2 is an exploded view of a flow element;

FIG. 3 is a side perspective view of a clamp;

FIG. 4 is a cross-sectional view of a filter and an gasket;

FIG. 5 is a top perspective view of the flow element;

FIG. 6 is a side perspective view of the flow element shown in FIG. 1;

FIG. 7 is a side perspective view of a respiratory module including theflow element shown in FIG. 1;

FIG. 8 is an exploded view of the flow element and a pressuretransducer;

FIG. 9 is a graph of a signal combining a breathing signal of a patientand a pulse having multiple frequencies;

FIG. 10 is a graph of a Fast Fourier Transform of the signal shown inFIG. 9;

FIG. 11 is a flowchart of a method for determining a therapy efficacy;

FIG. 12 illustrates graphs of a patient's lung resistance and lungreactance prior to therapy;

FIG. 13 illustrates graphs of a patient's lung resistance and lungreactance during therapy;

FIG. 14 illustrates graphs of a patient's lung resistance and lungreactance after therapy;

FIG. 15 is a graph of a patient's breathing cycle;

FIG. 16 is another graph of a patient's breathing cycle;

FIG. 17 is a flowchart of a method for removing artifacts from a graphof a patient's breathing cycle;

FIG. 18 illustrates a graph of a patient's lung resistance;

FIG. 19 illustrates a graph of a patient's lung reactance;

FIG. 20 is a perspective view of another embodiment of a flow element;

FIG. 21 is a top plan view of the flow element shown in FIG. 20;

FIG. 22 is a side perspective view of the filter shown in FIG. 21; and

FIG. 23 is a top plan view of the filter shown in FIG. 22.

DETAILED DESCRIPTION

According to the disclosed embodiments, by sending a pressure pulse thatcontains multiple frequencies into the patients' lung, pressure and flowsignals are collected, which represent the pressure drop acrosspatient's respiratory system as well as the flow rate into and out fromthe patients' lung. The pressure pulse signal contains 5-25 Hz, whichdoes not overlap with the patient's breathing frequency and is easilyseparated out using a Fast Fourier Transform (FFT). In addition, a 5-25Hz pressure signal is spread out from the patient's upper airway down tothe lower airway. By analyzing the pressure and flow relationship, thepatient's lung impedance is derived, which includes both resistance andreactance information. This technique to derive the patient's airwayimpedance condition is employed to objectively assess an airwayclearance device's therapy efficacy by analyzing an impedance curvechange after stage 1 therapy (mucus is mobilized from lower airway toupper airway) and stage 2 therapy (mucus is facilitated to cough out).Data is sent to a remote computer for both patients and caregivers toassess. Based on the therapy efficacy assessment, clinicians decidewhether a change in the therapy setting is needed or desired.

The disclosed embodiments also provide a three layer checking mechanismin the detection algorithm. In the first layer, deviation of the signalfrom the baseline is used as the main criteria to identify potentialartifacts. The baseline is updated once a new baseline is found. In thesecond layer, the detected artifacts with continuous presence of lessthan two data points will be rejected as a false detection. In the thirdlevel, a breathing waveform is mapped onto the real time impedance curveto identify the intact breathing cycles. Breathing cycles contaminatedby one or more artifacts will be rejected. The intact breathing cyclesare connected to calculate the impedance, and a counter is set up tocount the number of clean breathing cycles through detection ofinhalation and exhalation based on detection of a slope change in theflow rate and pressure waveform. In some embodiments, a minimum numberof breathing cycles of 8 may be used to ensure quality of the data.

The artifact detection/rejection mechanism is used to achieve accurateimpedance measurement. Without this mechanism, the impedance measurementof the patient's lung will be contaminated by the artifacts and,therefore, lead to inaccurate results. If enough clean breathing cycles(flow rate, pressure) remain after the contaminated breathing cycles arerejected, accurate results are achieved.

A respiratory device 10 is provided in FIG. 1. The details of thestructure of a suitable respiratory device and related electricalcomponents may be found in International Application No.PCT/SG2016/050166, filed Apr. 1, 2016, published as WO 2016/159889 A1 onOct. 6, 2016, and titled “Manifold for Respiratory Device,” which ishereby incorporated herein in its entirety. See also U.S. patentapplication Ser. No. 15/901,114, filed Feb. 21, 2018, which is herebyincorporated herein in its entirety. Respiratory device 10 includes ahousing 12 having a front wall 14 on which a display or graphical userinterface 16 is accessible to enter user inputs into device 10 and toview displayed information regarding the operation of device 10 as shownin FIG. 1. At a bottom region of front wall 14 of housing 12, a hose isattached to a flow element 24. Beneath the graphical user interface 16there is an on/off button 28 that is pressed sequentially to turn device10 on and off.

Device 10 is operable as an insufflation/exsufflation device or, as suchdevices are sometimes called, a cough assist device. Thus, device 10 iscapable of applying positive pressure and negative pressure to apatient's airway, the positive pressure being applied duringinsufflation and the negative pressure being applied duringexsufflation. The device 10 may be controlled to apply the positiveinsufflation pressure or the negative insufflation pressure to thepatient through a patient interface (not shown) that is coupled to theflow element 24. The user may select to switch between insufflation,exsufflation, and pause pressures in a manual mode of the device 10 orthis is done automatically by device 10 in an automatic mode. In someembodiments, device 10 is operable to provide other modes of respiratorytherapy such as continuous positive expiratory pressure (CPEP) andcontinuous high frequency oscillation (CHFO), just to name a couple.CPEP and CHFO are sometimes referred to herein, collectively, asIntrapulmonary Percussive Ventilation (IPV).

Referring to FIG. 2, the flow element 24 includes an inlet segment 52that is configured to couple to an outlet segment 54. The inlet segment52 includes a rounded body 56 and an inlet port 58 extending from therounded body 56. The rounded body 56 includes a retaining flange 60 thatis configured to facilitate coupling the inlet segment 52 to the outletsegment 54, as described below. A flange 42 extends around the roundedbody 56. The flange 42 steps down to an inner surface 62. A plurality ofnotches 64 extend from the inner surface 62 into the flange 42.

The outlet segment 54 includes a rounded body 70 and an outlet port 72extending from the rounded body 70. The outlet port 72 is configured tobe coupled to a patient interface via a hose. The rounded body 70includes an annular retaining flange 74 that is configured to facilitatecoupling the inlet segment 52 to the outlet segment 54. A pair of clamps76 is configured to engage the retaining flanges 60, 74 to secure theinlet segment 52 to the outlet segment 54. A flange 44 extends aroundthe rounded body 70 and steps down to an inner surface 68. A pluralityof tabs 66 extend from the flange 44. When the outlet segment 54 iscoupled to the inlet segment 52, the flanges 42 and 44 are abuttedagainst one another. The tabs 66 are secured within the notches 66 toalign the inlet segment 52 and the outlet segment 54. The inner surfaces62 and 68 define a cavity within the flow element 24.

Referring to FIG. 3, the clamps 76 include a tongue and grooveconfiguration to couple the outlet segment 54 to the inlet segment 52.An end 78 of each clamp includes a groove 92 and a tongue 94 extendingoutward from the groove 92. Likewise, as shown in FIG. 5, the flange 60also includes a tongue and groove configuration. Each end 46 includes agroove 96 and a tongue 98 extending from the groove 96. The tongues 94of each clamp 76 are configured to secured within the groove 96 of theflange 60. Also, the tongues 98 of the flange 60 are configured to lockwithin the groove 92 of each clamp 76.

A filter 80 is configured to position between the inlet segment 52 andthe outlet segment 54. The filter 80 positions between the rounded body56 of the inlet segment 52 and the rounded body 70 of the outlet segment54 when the inlet segment 52 is coupled to the outlet segment 54. Thefilter 80 is retained in the cavity defined by the inner surfaces 62 and68. In some embodiments, the filter 80 includes a screen 82 surroundedby an outer rim 84. The screen 82 and the outer rim 84 may be formedfrom metal or plastic. In some embodiments, the screen 82 may be a paperfilter. A gasket 86 includes a groove 88 that is configured to receivethe outer rim 84 of the filter 80. The gasket 86 seals the filter withinthe flow element 24 so that any air passing through the flow element 24passes through the screen 82. Referring to FIG. 4, the gasket 86 sealsaround the outer rim 84 and a portion of the screen 82 to seal the flowelement 24. Flow element 24 is sometimes referred to as apneumotachometer or a pneumotach, for short.

Referring to FIG. 6, when the inlet segment 52 is coupled to the outletsegment 54, the inlet port 58 and the outlet port 72 form a flowpath 90through the flow element 24. In some embodiments, the flowpath 90 is alinear flowpath between the inlet port 58 and the outlet port 72. Theflowpath 90 passes through the filter 80.

An inlet pressure port 100 extends from the rounded body 56 of the inletsegment 52. The inlet pressure port 100 extends parallel to the inletport 58. An outlet pressure port 102 extends from the round body 70 ofthe outlet segment 54. The outlet pressure port 102 extends parallel tothe outlet port 72. In the illustrative embodiment, the inlet pressureport 100 and the outlet pressure port 102 are aligned along an imaginaryline 104. The imaginary line 104 extends parallel to the flowpath 90.That is, the inlet pressure port 100 and the outlet pressure port 102extend parallel to the flowpath 90. The inlet pressure port 100 and theoutlet pressure port 102 are configured to couple to a differentialpressure sensor (described below).

Referring to FIG. 7, the flow element 24 is positioned within a housing120 that is configured to be positioned within the respiratory device10. A printed circuit board 128 is positioned within the housing 120 andincludes a pair of differential pressure sensors 130, 132. Referring toFIG. 8 a conduit 134 connects the outlet pressure port 102 to a firstdifferential pressure sensor 130 of the circuit board 128. A conduit 136connects the inlet pressure port to the first differential pressuresensor 130 and the second differential pressure sensor 132 through aY-splitter 138. The first differential pressure sensor 130 is configuredto output the pressure drop passing through the flow element 24 toderive a flow based on the resistance of the flow element 24. The seconddifferential pressure sensor 132 is configured to output a pressure dropacross the patients' airway system. In one embodiment, the firstdifferential pressure sensor 130 is a model number HSCMRRN016MD2A3differential pressure sensor, and the second differential pressuresensor 132 is a model number HSCMRRN160MDSA3 differential pressuresensor, both available from Honeywell International Inc. of MorrisPlains, New Jersey.

Based on the information derived from the differential pressuretransducers 132, 130, an efficacy of the therapy administered to thepatient from the respiratory device 10 is determined by passing pulsesthrough the flow element 24. Referring to FIG. 9, three graphs are shownincluding a graph 140 of the patient's breathing waveform 148 inpressure 144 over time 146 and a graph of an external stimulus appliedto the flow element 24 in the form of an impulse signal 142 containingmultiple frequencies, as shown in the bottom right graph of FIG. 9. Bycombining the waveform 142 and the impulse signal 148, a combined signal150 is acquired, as show in the third graph of FIG. 9, which can be usedin evaluating a patient's mechanical response to the impulse signal 148.FIG. 10 illustrates the combined signal 150 converted by a Fast FourierTransform, as shown in the left graph of FIG. 9. The Fast FourierTransform graph 152 illustrates a power spectrum 154 as a function offrequency 156. As illustrated in FIG. 10, the patient's breathing cycleis represented by a peak 158 having frequency of approximately 0.5 Hz.The impulse signal 148 is represented by a peak 160 having a higherfrequency of about 5 Hz.

Based on the graph 152, a respiratory system impedance can be derivedwhich gives the information on the patients' lung resistance andcompliance using the below equations:

Zrs(ω) = P(ω)/V^(′)(ω) = Rrs + iXrs = Rrs + i(ω I − 1/ω C)

Zrs(ω) represents an impedance of the patient's breathing cycle, Rrsrepresents the patient's lung resistance in cmH2Os/L, which is a measureof pressure divided by flowrate, and Xrs represents the patient's lungreactance in cmH2Os/L. Additionally, I represents a patient's lunginertia and C represents the patient's lung compliance. Notably, lowfrequency oscillations (f<20 Hz) are spread in a lower depth of theairway, and higher frequency oscillations (f>20 Hz) are spread in anupper portion of the airway. Accordingly, the patient's lung resistanceand lung reactance before treatment are compared to the patient's lungresistance and lung reactance after therapy using the method shown inFIG. 11.

At block 170 of FIG. 11, the impulse signal 148 is introduced to thepatient's airway. The patient's lung impedance is calculated using theequation set forth above, at block 172. Based on the patient's lungimpedance an assessment of the patient's lung condition is evaluated, asindicated at block 174. The therapy is then delivered to the patient, atblock 176. After therapy, another impulse signal 148 is introduced intothe patient's airway to derive a new patient lung impedance, at block178. At block 180, the new lung impedance is compared to the lungimpedance prior to the therapy to assess the efficacy of the therapy.

For example, FIG. 12 illustrates a lung resistance curve 190 and lungreactance curve 192 at stage 1 of therapy during mucus mobilization whenmucus in moved from the lower airway to the upper airway. The lungresistance curve 190 and the lung reactance curve 192 are shown in unitsof centimeters of water seconds per liter (cmH2Os/L) along the y-axis,and are illustrated over frequency in Hz along the x-axis. In the lungresistance curve 190, the point 200 represents an overall resistance ofthe respiratory system at a frequency of 5 Hz. The point 202 representsthe resistance of the conducting airways at 20 Hz. The line from point200 to point 202 represents changes in the shape of resistance that aretypically associated with heterogeneous obstruction and small airwaydisease. In the lung reactance curve 192, the point 210 representsoverall stiffening (i.e. loss of compliance) of the lungs andobstruction of small airways at a frequency of 5 Hz. The point 212represents the frequency (10 Hz) at which the reactance is zero, whichis indicative of an overall stiffening of the lungs and obstruction ofsmall airways. The area 214 is indicative of overall stiffening of thelungs and obstruction of small airways. Lastly, a change in the point210 represents the difference between low frequency inspiratory andexpiratory resistance.

FIG. 13 illustrates a lung resistance curve 220 and a lung reactancecurve 222 at stage 2 of therapy, when mucus is facilitated to cough outof the patient's airway. If the therapy is effective, the followingtrends should be observed. The resistance at 20 Hz should increase asshown by point 224 indicating an increase in upper airway resistance.Likewise, the resistance at 5 Hz should increase as illustrated by point226. The line 228 between 5 Hz and 20 Hz should decrease indicating thatthe lower airway resistance has decreased relative to the initial curve190. Further, in the lung reactance curve 222, the new curve 230 shouldshift upward, relative to the initial curve 192, indicating improvedlung compliance.

FIG. 14 illustrates a lung resistance curve 240 and a lung reactancecurve 242 at stage 3 after the therapy has ended. After therapy, thefollowing trends should occur if the therapy is effective. Theresistance at 20 Hz should decrease as represented by point 250. Theresistance at 5 Hz should decrease as represent by point 252. Also, thenew curve 254 from 5 Hz to 20 Hz should decrease, relative to the curve220. Each of these decreases is indicative of a decrease in both theupper airway and lower airway resistance. Further, the new reactancecurve 260 will shift upward, relative to the curve 230, indicatingimproved lung compliance.

While the above method may be utilized to determine the efficacy of atherapy treatment, there may be several factors that may affect thedata. For example, a nose clip, a cheek support, sitting posture of thepatient, or motion of the patient may create artifacts in the impedancedata. Also, additional tubing, bending in the tubing, or an exhalationport may create artifacts. Artifacts may also be created by glottisclosure, coughs, swallowing, or other breathing artifacts. For example,FIG. 15 illustrates a breathing pressure waveform 300 and a resistancecurve 302 at 20 Hz as a function of pressure 304 (y-axis) over time 306(x-axis). Artifacts are indicated by the line 308. As can be seen, anartifact 320 occurs between 0.5 seconds and 1.5 seconds that may beindicative of leakage in the system. Another artifact 322 occurs between2.5 seconds and 4 seconds that may be indicative of blockage in thesystem. In another example, FIG. 16 illustrates a breathing pressurewaveform 330 and a resistance curve 332 at 5 Hz as a function ofpressure 334 (y-axis) over time 336 (x-axis). An artifact 340 is presentat 0.5 seconds, which may be indicative of coughing. Another artifact342 is present between 1 second and 2 seconds, which may be indicativeof burping. An artifact 344 is present at 2.5 seconds, which may beindicative of swallowing. Lastly, an artifact 346 is present at 3.5seconds, which may be indicative of hemming.

FIG. 17 illustrates a method 400 for removing artifacts that occurs inthree stages. In the first stage, at block 402 a mean value iscalculated for 10 milliseconds of data. At block 404, a deviation in thedata is calculated by subtracting the original mean value from a newlyacquired mean value and dividing by the original mean value to determinea percentage of deviation. It is then determined whether the deviationis greater than 13%, at block 406. It should be noted that otherpercentages may be utilized to assess the data. At block 408, adeviation greater than 13% is flagged, and the original mean value isupdated with the new mean value, at block 410. If at block 406 thedeviation is not greater than 13%, the method proceeds to block 420.

In the second stage, at block 420, further deviation values are detecteduntil all of the artifact points are detected. At block 422, the data isassessed to determine whether any consecutive artifact points exist. Ifso, these points are flagged as real artifacts. At block 424, artifactpoints that are not consecutive are flagged as false alarms. At block426, the breathing cycle is detected in the pressure flowrate waveformlike those in FIGS. 9-11. Inhaling and exhaling is flagged by adding thezero crossing point to the positive slope to acquire a sum, and dividingthe sum by the negative slope.

In the third stage, the artifacts are mapped onto the breathing curve,and if an artifact is embedded in the breathing cycle, the breathingcycle is rejected, at block 430. At block 432, the impedance iscalculated only for valid breathing cycles and the results are connectedtogether to determine a curve without artifacts. FIGS. 15 and 16illustrate resistance and reactance curves, respectfully, both with andwithout the artifacts.

Referring to FIG. 18, a patient's lung resistance is illustrated asresistance 450 as a function of frequency 452. A first line 454illustrates the lung resistance with an artifact. A second line 456illustrates the lung resistance without the artifact. At 5 Hz. frequencythe lung resistance is higher in line 454 than in line 456. Accordingly,by using the method set forth above to remove artifacts, the patientshows lower and improved lung resistance without the artifact, whencompared to the lung resistance with the artifact.

Referring to FIG. 19, a patient's lung reactance is illustrated aspressure 460 as a function of frequency 462. A first line 464illustrates the lung reactance with an artifact. A second line 466illustrates the lung reactance without the artifact. At 20 Hz. and 25Hz, the lung reactance is lower and improved without the artifact, whencompared to the lung reactance with the artifact. Accordingly, by usingthe method set forth above to remove artifacts, the patient shows lowerand improved lung reactance without the artifact, when compared to thelung reactance with the artifact.

FIG. 20 is another embodiment of a flow element 500 having a centralbody 502 and an inlet 504 and outlet 506 extending from the central body502. The inlet 504 has an end 508 with a diameter 510 that is less thana diameter 512 of the inlet 504 at the central body 502. The outlet 506has a diameter 514 that is equal to or greater than the diameter 512.This trumpet shape or dialation of inlet port to a much bigger diameterfacilitates achieving laminar flow so that the effective flow area isequivalent to the inlet port size. The central body 502 is sized toretain a filter 530 as illustrated in FIG. 21.

Referring to FIGS. 22 and 23, the filter 530 includes a gasket 532 thatseals a honeycomb 534 within the central body 502. The honeycomb 534includes a plurality of holes 536 having a diameter of approximately 0.9mm. The larger diameter reduces the chance of dust and/or moisturebecoming stuck in the holes 536 when compared to a mesh or screendesign. Accordingly, the user does not have to regularly clean the flowelement 500. The honeycomb 534 has a thickness 538 of approximately lcm.The thickness facilitates creating a desired pressure drop for sensingflow through the flow element 500.

Although this disclosure refers to multiple embodiments, it will beappreciated that aspects of each embodiment may be utilized with otherembodiments described herein.

Although this disclosure refers to specific embodiments, it will beunderstood by those skilled in the art that various changes in form anddetail may be made without departing from the subject matter set forthin the accompanying claims.

1. A respiratory device comprising: an inlet port and an outlet port; afluid pathway extending between the inlet port and the outlet port; afilter housing positioned between the inlet port and the outlet port; afilter positioned within the filter housing; a first pressure portpositioned on an inlet side of the filter housing; a second pressureport positioned on an outlet side of the filter housing, wherein thefirst pressure port and the second pressure port extend parallel to thefluid pathway; and a pressure transducer coupled to the first pressureport and the second pressure port and configured to measure a pressuredrop between the first pressure port and the second pressure port. 2.The respiratory device of claim 1, wherein the filter is positionedbetween the first pressure port and the second pressure port.
 3. Therespiratory device of claim 1, wherein the filter includes at least oneof a screen or a honeycomb.
 4. The respiratory device of claim 1,further comprising a gasket extending around the filter.
 5. Therespiratory device of claim 4, wherein the gasket seals an inlet sideand an outlet side of the filter.
 6. The respiratory device of claim 4,wherein the gasket prevents airflow around the filter.
 7. Therespiratory device of claim 1, wherein the inlet port is coupled to arespirator.
 8. The respiratory device of claim 1, wherein the filterhousing includes an inlet segment including the inlet port and an outletsegment including the outlet port.
 9. The respiratory device of claim 8,wherein the inlet segment and the outlet segment are coupled together.10. The respiratory device of claim 9, further comprising a clamp tocouple the inlet segment to the outlet segment.
 11. The respiratorydevice of claim 10, wherein the clamp seals the inlet segment to theoutlet segment.